Transdermal dosage form for low-melting point active agent

ABSTRACT

A drug-containing patch allows transdermal administration of a drug. The patch features a hydrophobic reservoir containing the drug, where the reservoir has a first surface and a second surface. A drug-impermeable backing overlies the first surface of the reservoir. A release sheet may overlie the second surface of the reservoir. The hydrophobic reservoir contains a drug and a hydrophobic matrix, where the hydrophobic matrix includes a hydrophobic filler in an amount which is effective to adsorb said drug; and a mixture of polyisobutylene and mineral oil. The hydrophobic matrix may contain hydrophobic colloidal silica as the hydrophobic filler. 
     The hydrophobic reservoir layer may serve as a skin-contacting adhesive layer. Alternatively, a release-controlling adhesive layer may serve as the skin-contacting adhesive layer. The release-controlling adhesive layer may contain hydrophobic colloidal silica and a mixture of polyisobutylene and mineral oil.

BACKGROUND

1. Field of the Invention

The current disclosure is directed to pharmaceutical preparations,particularly pharmaceutical preparations for manufacturing transdermalpatches.

2. Description of Related Art

“Drug-in-adhesive” transdermal systems contain a drug-containingadhesive polymer layer, a drug-impermeable backing layer overlying oneside of the adhesive layer, and a release layer, such as asilicone-coated paper layer, overlying the other side of the adhesivelayer. Generally, in “drug-in-adhesive” transdermal systems, theadhesive polymer forms an outer or continuous phase. Variouspharmacologically inactive ingredients, such as fillers or plasticizers,may be dissolved or dispersed in the polymeric matrix. Suitable adhesivepolymers may include hydrophobic polymers, such as polyisobutylenes or(meth)acrylate ester polymers. The adhesive polymers, together withfillers, plasticizers, and other pharmacologically inactive ingredients,make up an adhesive hydrophobic matrix.

The pharmacologically active ingredients can be either dissolved ordispersed in the hydrophobic matrix. The solubility and the physicalproperties of the active pharmaceutical ingredient are of greatimportance in influencing the physical as well as the drug deliveryperformance of the transdermal system.

Many active pharmaceutical ingredients are able to undergo changes intheir physical form during processing, i.e., from one polymorph toanother or from solid to liquid. Such changes in physical form can giverise to several issues during processing or manufacturing. These includeissues of crystallization or re-crystallization. In some cases, exposureto high temperatures or pressures during processing can lead to changesin the physical form of the active pharmaceutical ingredient. Forexample, a crystalline drug with a low melting point may be added to anadhesive composition which is then subjected to further processing. Theadhesive composition may be subjected to heat or pressure during anextrusion process to form an adhesive layer, causing the drug to melt.Upon cooling of the adhesive composition after extrusion, the drug maysolidify in an amorphous form, or in a crystalline polymorphic formwhich is different from its original form. In other cases, the drug mayform an oil which is dispersed through the adhesive matrix.

Such changes in the physical form of the drug can affect the transdermalsystem as a whole. For example, if the active pharmaceutical ingredienthas a low melting point and converts from its solid state to an oilstate during processing, the oil state of the active ingredient canplasticize the adhesive matrix. Plasticizing the adhesive matrix can inturn cause delamination of the adhesive matrix from the drug-impermeablebacking or from the release layer. Also, plasticizing the adhesivematrix can cause “cold flow,” defined as distortion, deformation, ordimensional change at normal temperatures during storage conditions.

Additionally, if the active pharmaceutical ingredient is in oil form andis not sufficiently adsorbed in the adhesive matrix, or adsorbed by anexcipient in the matrix, the oil can diffuse through the matrix and cancause film deposition or deposition of oil at the interface between theadhesive and the release liner interface. Diffusion of an oil throughthe adhesive matrix can also cause delamination and cold flow issuesduring storage.

Additionally, an adhesive layer may serve as a rate-limiting layer tocontrol diffusion of oily drugs and other plasticizing agents from thedrug reservoir to the interface between the reservoir and the backing.

There are known US marketed drug-in-adhesive transdermal products whichcontain a combination of polyisobutylene, mineral oil and colloidalsilica as a transdermal matrix containing a drug such as scopolamine,clonidine or SALONPAS®. It has been claimed that the colloidal silicaincreases the viscosity in these products. It has also been claimed thatthe colloidal silica increases the permeability of the matrix,especially in transdermal products containing scopolamine or clonidine.

The present disclosure describes various embodiments, but is notintended to be exhaustive or limiting of the possible advantages thatcan be realized. Thus, the various embodiments are not intended to limitthe scope of the invention. Accordingly, the present invention residesin the novel methods, arrangements, combinations, and improvementsherein shown and described in various embodiments.

SUMMARY

In light of the present need for improved transdermal dosage forms forlow-melting or highly diffusible drugs, a brief summary of variousexemplary embodiments is presented. Some simplifications and omissionsmay be made in the following summary, which is intended, to highlightand introduce some aspects of the various exemplary embodiments, but notto limit the scope of the invention. Detailed descriptions of apreferred exemplary embodiment adequate to allow those of ordinary skillin the art to make and use the inventive concepts will follow in latersections.

In a broad perspective, the transdermal systems disclosed herein includeexcipients which can substantially adsorb the drug molecules to overcomethe deposition of oil or film formation at the adhesive-release linerinterface or at the adhesive-backing layer interface. In certainembodiments, drug-in-adhesive transdermal systems can use silicaparticles as excipients to adsorb drug particles. In variousembodiments, drug-in-adhesive transdermal systems can use hydrophobicexcipients, including hydrophobic colloidal silica, to adsorb particlesof hydrophobic drugs. In various embodiments, drug-in-adhesivetransdermal systems can use more hydrophilic excipients, includingconventional colloidal silica, to adsorb particles of hydrophilic drugs.Combinations of excipients may be used.

In various embodiments, the excipient is hydrophobic colloidal silica.Transdermal patches can be constructed with different levels ofhydrophobic colloidal silica material by which the physical performanceas well as the drug delivery performance of the patch can be altered.Transdermal compositions may include drug reservoir layers comprisingpolyisobutylene (high and low molecular weight), mineral oil,hydrophobic colloidal silica and the active pharmaceutical ingredient.Additionally, this composition involves a dependency between the choiceof the level of hydrophobic colloidal silica material and the physicalperformance of the transdermal patch.

In a first aspect, the current application is directed to laminating anadhesive layer to a drug reservoir layer to produce a transdermalsystem. In various embodiments, the rate of drug delivery can becontrolled by the adhesive layer. Also, the current application isdirected to a process by which the lamination of the adhesive layer tothe drug reservoir layer can improve the physical performance of thetransdermal system. The current specification also pertains to atransdermal composition which contains polyisobutylene (high and lowmolecular weight), mineral oil, hydrophobic colloidal silica and theactive pharmaceutical ingredient in the drug reservoir layer andpolyisobutylene (high and low molecular weight), mineral oil, andhydrophobic colloidal silica in the adhesive layer, also referred to asthe skin contact layer.

The current disclosure relates to a patch for transdermal administrationof a drug, comprising a hydrophobic reservoir containing the drug, wherethe reservoir has a first surface and a second surface. In variousembodiments, a backing overlies the first surface, where the backing isimpermeable to the drug. In certain embodiments, the hydrophobicreservoir layer is the outermost layer of the patch, and serves as askin-contacting adhesive layer. In some embodiments, a release sheetoverlies the second surface of the reservoir.

In various embodiments, the hydrophobic reservoir contains a drug and ahydrophobic matrix, where the hydrophobic matrix contains a hydrophobicfiller in an amount which is effective to adsorb said drug; and amixture of polyisobutylene and mineral oil. In various embodiments, thepolyisobutylene and mineral oil are used in a weight ratio of mineraloil to polyisobutylene of at least about 0.05:1, at least about 0.25:1,or at least about 0.301. In various embodiments, the polyisobutylene andmineral oil are used in a weight ratio of mineral oil to polyisobutyleneof up to about 1:1, up to about 0.60:1, or up to about 0.50:1. Invarious non-limiting embodiments, the weight ratio of mineral oil topolyisobutylene may be between about 0.05:1 and about 1:1. In variousnon-limiting embodiments, the weight ratio of mineral oil topolyisobutylene may be between about 0.25:1 and about 0.60:1. In variousnon-limiting embodiments, the weight ratio of mineral oil topolyisobutylene may be between about 0.30:1 and about 0.50:1. Thehydrophobic matrix may contain from 6% to 30% by weight of the reservoirof hydrophobic colloidal silica as a hydrophobic filler. In variousembodiments, the drug and the hydrophobic filler may be present in aweight ratio of between about 2:1 and about 0.9:1.

In various embodiments, the patch for transdermal drug administrationcomprises a hydrophobic reservoir containing the drug (the drugreservoir layer), where the reservoir has a first surface and a secondsurface, and a release-controlling adhesive layer in contact with saidsecond surface of the reservoir. A drug-impermeable backing overlies thefirst surface. In certain embodiments, the release-controlling adhesivelayer is the outermost layer of the patch. In some embodiments, arelease sheet overlies the second surface of the reservoir, with therelease-controlling adhesive layer being between the reservoir and therelease sheet.

In various embodiments, the patch includes a release-controllingadhesive layer laminated to the drug reservoir layer, where therelease-controlling adhesive layer comprises from 0.5% to 5% by weightof said release-controlling adhesive layer of hydrophobic colloidalsilica; and a mixture of polyisobutylene and mineral oil in a weightratio of polyisobutylene to mineral oil of between about 1:1 and about4:1. The release-controlling adhesive layer contains a smaller amount ofhydrophobic colloidal silica than the drug reservoir layer. In variousembodiments, the hydrophobic matrix in the drug reservoir layer of thepatch comprises from 8% to 20% by weight of the drug reservoir layer ofhydrophobic colloidal silica; and the release-controlling adhesive layercomprises from 0.5% to 5% by weight of the release-controlling adhesivelayer of hydrophobic colloidal silica. The hydrophobic colloidal silicamay have a particle size of between 30 nm and 150 nm, although othersizes are also suitable. The hydrophobic silica may be colloidal silicawhich has been treated with a silane of formula I:R_((4-n))SiX_(n)  Iwhere R is a C1 to C20 alkyl or aromatic group, X is a hydrolysablegroup, and n is 1, 2, or 3. In various embodiments, X is —OH, —O₂CR¹,—Cl, —Br, —I, —OR¹, —COR¹, —NHR¹, or NR¹ ₂, where R¹ is a C1 to C20alkyl or aromatic group.

In various embodiments, the hydrophobic reservoir in the patch containsa low-melting drug, e.g., a drug having a melting point of between 20°C. and 150° C., or between 20° C. and 80° C. Suitable low-melting drugsinclude methylphenidate, ibuprofen, clonidine, or scopolamine. Invarious embodiments, the hydrophobic reservoir in the patch contains ahydrophobic drug which is able to diffuse through the hydrophobicmatrix, where the diffusible hydrophobic drug may or may not be alow-melting drug. In various embodiments, the hydrophobic drug iscapable of adsorbing to the surface of a hydrophobic filler oradsorbent, such as hydrophilic colloidal silica.

DETAILED DESCRIPTION OF VARIOUS DISCLOSED EMBODIMENTS

This disclosure describes a process by which, in a transdermal system,an adhesive layer can be laminated to a drug reservoir layer. Theresulting transdermal system allows the rate of drug delivery to becontrolled. Also, this disclosure pertains to a process by whichlamination of an adhesive layer with varied thickness to a drugreservoir layer can improve the physical performance of the transdermalsystem. The invention also pertains to a transdermal composition whichcontains polyisobutylene (high and/or low molecular weightpolyisobutylene), mineral oil, hydrophobic colloidal silica and anactive pharmaceutical ingredient. The active pharmaceutical ingredientis included in a drug reservoir layer, where the drug reservoir layercontains a hydrophobic polymeric matrix containing polyisobutylene,which may be high molecular weight polyisobutylene, low molecular weightpolyisobutylene, or a mixture thereof; mineral oil, and hydrophobiccolloidal silica.

The polyisobutylene may be high molecular weight polyisobutylene, lowmolecular weight polyisobutylene, or a mixture thereof. The highmolecular weight polyisobutylene may have an average molecular weight of500,000 to 1.5 million, or from 750,000 to 1.2 million. The lowmolecular weight polyisobutylene may have an average molecular weight of40,000 to 85,000. Suitable polyisobutylene adhesives include Oppanol B80(a high molecular weight PIB), Oppanol B100 (a high molecular weightPIB), Oppanol B12 (a low molecular weight PIB), and Duro-Tak 87-613A (amixture of high and low molecular weight PIBs). For adhesives using amixture of high and low molecular weight PIBs, the ratio of highmolecular weight to low molecular weight PIB may range from 0.5:1 to1.5:1; 0.6:1 to 1.1:1; or about 0.8:1. The active pharmaceuticalingredient is included in a drug reservoir layer, where the drugreservoir layer contains a hydrophobic polymeric matrix containingpolyisobutylene, which may be high molecular weight polyisobutylene, lowmolecular weight polyisobutylene, or a mixture thereof, mineral oil, andhydrophobic colloidal silica.

Generally, in “drug-in-adhesive” transdermal systems, the adhesivepolymer is considered as the outer or continuous phase. Thepharmacologically inactive ingredients are dissolved or dispersed in theadhesive polymer and the pharmacologically active ingredients can beeither dissolved or dispersed in the adhesive polymer as well. Thesolubility and the physical properties of the active pharmaceuticalingredient are of great importance in influencing the physical as wellas the drug delivery performance of the transdermal system.

During processing or manufacturing, the active pharmaceutical ingredientmay undergo changes in its physical state. These changes includecrystallization/re-crystallization and/or conversion of a drug having adefined physical form into a different physical form. Such changes inthe drug can in turn affect the transdermal system as a whole. Forexample, if the active pharmaceutical ingredient has a low melting pointand is heated above its melting point during processing, the activepharmaceutical ingredient can be converted from a solid state to aliquid or oily state during processing. The liquid or oily form of theactive pharmaceutical ingredient can plasticize the matrix and can causedelamination during the manufacturing process. Further, the oily orliquid active pharmaceutical ingredient can diffuse through the matrixof the transdermal system and can cause film deposition or deposition ofoil at the adhesive-release liner interface.

To overcome these problems, an excipient may be added to the matrix. Asuitable excipient should have a significant adsorption capacity for theactive ingredient. Other factors include the interaction of theexcipient with the active pharmaceutical ingredient, as well as theintroduction of impurities by the excipient. Optimization of thesefactors is often performed in the manufacture of a physically acceptabletransdermal system. Failure to properly address these factors can causeinferior performance of a transdermal system, even though other aspectsof the formulation are thoroughly optimized.

For example, some drugs are subject to degradation by hydrolysis. Theextent of drug degradation by hydrolysis is mainly determined by themoisture present in the carrier in addition to other moistureintroducing factors. In a transdermal system containing a hydrophobicmatrix such as polyisobutylene/mineral oil matrix, little moisture iscontributed by the hydrocarbon polymers and oils. However, colloidalsilica is hydrophilic, and contains water adsorbed on the silicaparticles. The amount of moisture present or adsorbed on the silicaparticles can directly influence the stability of the adsorbed drug.Accordingly, colloidal silica may not be the ideal excipient foradsorbing a drug which is subject to hydrolysis, as the drug may bebound in close proximity to adsorbed water. Further, colloidal silicahas a hydrophilic surface which may repel hydrophobic drugs. To addressthese issues, a hydrophobic adsorbent may be used with a hydrophobicdrug or a drug which undergoes hydrolysis readily. Hydrophobic colloidalsilica is a possible example of a hydrophobic adsorbent.

Colloidal silicon dioxide, also known as colloidal silica, is anexcipient approved by the Food and Drug Administration (FDA) as a GRAS(Generally Regarded As Safe) material for use in topical pharmaceuticalpreparations. Because of its valuable properties like large surfacearea, low density and small particle size, it is well recognized asbeing capable of adsorbing some active pharmaceutical ingredients. Theadsorptive nature of the silica particles is a significant factorcontributing to their use as carriers in some pharmaceuticalpreparations.

In certain embodiments, the transdermal system contains a single-layeradhesive system. The reservoir layer is an adhesive material and has twomajor surfaces. A drug-impermeable backing layer is laminated to onemajor surface of the reservoir layer; and a release liner, such as asilicone-coated paper layer, is releasably laminated to the other majorsurface of the reservoir layer. The release liner may be peeled off ofthe reservoir layer to reveal an adhesive surface of the reservoirlayer. The exposed adhesive surface may then be adhered to a skinsurface, allowing the drug to diffuse through the hydrophobic matrix ofthe reservoir matrix to the skin surface. In various embodiments, thereservoir layer contains a mixture of polyisobutylene and mineral oil ina weight ratio of mineral oil to polyisobutylene of between about 0.05:1and about 1:1. In various non-limiting embodiments, the weight ratio ofmineral oil to polyisobutylene may be between about 0.251 and about0.60:1. In various non-limiting embodiments, the weight ratio of mineraloil to polyisobutylene may be between about 0.30:1 and about 0.50:1. Thereservoir layer may contain from 6% to 30% by weight of the reservoir ofhydrophobic colloidal silica as a hydrophobic filler.

In certain embodiments, the reservoir layer is laminated to an adhesivelayer to produce a bilayer adhesive system. The adhesive layer may alsobe referred to as the skin contact layer or as the skin-contactingadhesive layer. In embodiments containing both a reservoir layer and askin-contacting adhesive layer, the reservoir layer and theskin-contacting adhesive layer are laminated together. In variousembodiments, the reservoir layer contains from about 8% to about 30% byweight of the active ingredient; a drug-adsorbing excipient, such ashydrophobic colloidal silica; and a mixture of polyisobutylene andmineral oil in a weight ratio of said polyisobutylene to said mineraloil of between about 1:1 and about 4:1. In various embodiments, thereservoir layer contains from about 8% to about 30%, or about 8% toabout 20%, by weight of the reservoir layer of hydrophobic colloidalsilica as a drug-adsorbing excipient. The skin-contacting adhesive layercontains from about 0.5% to about 5%, or about 1% to about 3%, by weightof the release-controlling adhesive layer of hydrophobic colloidalsilica; and a mixture of polyisobutylene and mineral oil in a weightratio of said polyisobutylene to said mineral oil of between about 1:1and about 4:1. In certain embodiments, the skin-contacting adhesivelayer is free of any active ingredients.

Suitable excipients to be added to a drug reservoir layer which may beused to adsorb drugs include, in amounts by weight of the reservoirlayer:

hydrophobic colloidal silica in an amount of about 8% to about 30%;

a combination of hydrophobic colloidal silica in an amount of about 1%to about 3% and titania (titanium dioxide) in an amount of about 2%;

neusilin (magnesium aluminometasilicate) in an amount of about 2% toabout 5%;

a combination of neusilin (magnesium aluminometasilicate) in an amountof about 2% to about 5% and at least one of magnesium stearate in anamount of about 2% to about 5%, polyethoxylated castor oil in an amountof about 2% to about 5%, and a mixture thereof;

colloidal silica or dried colloidal silica in an amount of about 1% toabout 10%;

a combination of colloidal silica in an amount of about 1% to about 3%and neusilin in an amount of about 2%, magnesium stearate in an amountof about 1% to about 3%, disodium hydrogen phosphate in an amount ofabout 2% to about 5%, polyethoxylated castor oil in an amount of about2% to about 5%, or a mixture thereof;

disodium hydrogen phosphate in an amount of about 2% to about 5%;

anhydrous calcium phosphate dibasic in an amount of from 5% to about10%;

a combination of anhydrous calcium phosphate dibasic in an amount offrom 5% to about 10% and polyethoxylated castor oil in an amount ofabout 2% to about 5%;

polyethoxylated castor oil in an amount of about 2% to about 5%;

magnesium stearate in an amount of about 2% to about 5%;

clays such as kaolin in an amount of about 5% by weight;

up to 1% by weight of alpha-tocopherol; and

from about 5% to about 20% Eudragit EPO, a cationic copolymer based ondimethylaminoethyl methacrylate, butyl methacrylate, and methylmethacrylate.

in certain embodiments, polymers such as polyethylene glycol, polyvinylpyrrolidone or hydroxypropyl methylcellulose may be used as an adsorbentin an amount of between about 3% and 7% by weight.

In various embodiments, hydrophobic excipients may be used topreferentially adsorb hydrophobic drugs. Hydrophilic excipients may beused to adsorb less hydrophobic drugs.

Suitable hydrophobic excipients for use with hydrophobic drugs includehydrophobic colloidal silica; a combination of hydrophobic colloidalsilica and titania; polyethoxylated castor oil; and magnesium stearate.

Various embodiments disclosed herein use hydrophobic colloidal silica asa hydrophobic excipient. Conventional colloidal silica has a hydrophilicsurface with silanol groups. Although hydrophilic colloidal silica hasbeen used in transdermal systems, hydrophilic colloidal silica is a pooradsorbent for hydrophobic drugs, such as methylphenidate. To addressthis issue, the transdermal system disclosed herein uses a hydrophobiccolloidal silica as a filler and adsorbent. In various embodiments, thehydrophobic colloidal silica used as an adsorbent may be a chemicallymodified colloidal silica. In some embodiments, the colloidal silica hasbeen treated with a hydrolysable silane of formula I:R_((4-n))SiX_(n)  Iwhere R is a C1 to C20 alkyl or aromatic group, X is a hydrolysablegroup, and n is 1, 2, or 3. In various embodiments, X is —OH, —O₂CR¹,—Cl, —Br, —I, —OR¹, —COR¹, —NHR¹, or —NR¹ ₂, where R¹ is a C1 to C20alkyl or aromatic group. The hydrolysable silane is attached to thecolloidal silica by a condensation reaction between the —SiX_(n) groupon the silane and silanol groups on the colloidal silica, replacinghydrophilic silanol groups on the silica surface with hydrophobic alkylgroups.

Because of its excellent surface area hydrophobic colloidal silica caneffectively adsorb hydrophobic drugs and other hydrophobic ingredients.Also from a drug stability point of view in this process, the stabilityof the drug reservoir in the transdermal patch depends on theinteraction between the hydrophobic colloidal silica and the drug. Byusing hydrophobic colloidal silica at a certain percentage (from about6% to about 30%, preferably from about 8% to about 20% in theformulation) as an excipient, the diffusion of the active pharmaceuticalingredient through the matrix can be controlled during storage.Specifically, the hydrophobic drug and other hydrophobic ingredientsadsorb to the hydrophobic surface of the silica particles. When at leasta portion of the hydrophobic ingredients, i.e., from about 20% to about100% of the hydrophobic ingredients, adsorb to the hydrophobic silicasurface, this reduces or prevents free diffusion of the hydrophobicingredients, including hydrophobic drugs, through the hydrophobicmatrix. Reducing drug diffusion in this manner increases stability ofthe transdermal patch, as the drug does not diffuse to the surfaces ofthe hydrophobic reservoir layer. Thus, adsorption of the drug to thehydrophobic colloidal silica can be considered as a significant factorin controlling the diffusion of the drug molecules. In the absence ofhydrophobic colloidal silica, the hydrophobic drug, particularly liquidor oily drugs, may diffuse through the hydrophobic matrix to thesurfaces of the hydrophobic reservoir layer, establishing a layer ofdrug at the interface between the reservoir layer and adjacent layers.This can reduce adhesion between layers, leading to delamination of thelayers of the transdermal system.

Hydrophobic colloidal silica is used in various exemplary embodimentsdue to its excellent physicochemical and physiological properties.Hydrophobic colloidal silica has a large specific surface area for drugdeposition, as well as exhibiting strong adsorption to hydrophobicdrugs. Uniform distribution of the drug molecules and the hydrophobiccolloidal silica in the hydrophobic matrix of the drug reservoir can beensured with a well optimized mixing strategy which allows the drugmolecules to be uniformly distributed over the silica particles.However, the stability of the drug depends upon the impurities of theexcipient as well as the absorbed moisture by the excipient.

Drug degradation by hydrolysis is mainly determined by the moisturepresent in the pharmacologically active and inactive ingredients or bythe moisture present in the system. The amount of moisture present oradsorbed on the silica particles can directly influence the stability ofthe adsorbed drug.

The effect of drug-adhesive mixing in the presence of hydrophobiccolloidal silica was studied. With a drug reservoir containinghydrophobic colloidal silica in an amount of between about 8% and 20%,physical issues faced during the manufacturing process and duringaccelerated stability storage conditions were resolved, allowingproduction of an acceptable transdermal system. With a drug reservoircontaining hydrophobic colloidal silica in an amount of ≦5%, or with areservoir in which hydrophobic colloidal silica was absent, thesephysical issues were not successfully resolved. Even with a physicallyacceptable transdermal system, controlling the drug delivery performancewas a significant challenge.

This challenge was addressed by designing an adhesive layer with acomposition similar to the drug reservoir layer, where the adhesivelayer contains polyisobutylene (high and low molecular weight), mineraloil, and hydrophobic colloidal silica with varied percentages of eachcomponent.

The adhesive layer was laminated to a first major surface of the drugreservoir layer. By laminating the adhesive layer to the drug reservoirlayer, which includes polyisobutylene, mineral oil, activepharmaceutical ingredient and hydrophobic colloidal silica, anacceptable controlled rate of drug delivery may be attained. Adrug-impermeable backing layer was laminated to a second major surfaceof the reservoir layer.

In various embodiments, a protective layer covers the adhesive layer. Insome embodiments, the protective layer is a release sheet, such as asilicone-coated paper sheet, laminated to a surface of the adhesivelayer opposite the drug reservoir layer. In other embodiments, thedrug-impermeable backing layer may include a release layer coated on thesurface opposite the reservoir layer. The transdermal system is preparedin a form which may be stacked or rolled so that the release layer onthe drug-impermeable backing layer protects the adhesive layer on anadjacent transdermal system.

In various embodiments, the adhesive layer contains no drug at the timeof manufacturing. In some embodiments, the adhesive layer contains adrug in a low concentration which is less than the concentration of thedrug in the adjacent reservoir layer. The adhesive layer may contain alow concentration of drug as a result of drug diffusion from thereservoir layer to the adhesive layer subsequent to manufacturing.Alternatively, the adhesive layer may be manufactured with a lowconcentration of drug in the adhesive layer and a high concentration ofdrug in the reservoir layer. The hydrophobic colloidal silica in theadhesive layer is present in an amount of between about 0.5% and about5% by weight of the adhesive layer. In certain embodiments, thehydrophobic colloidal silica in the adhesive layer is present in anamount of between about 1% and about 3% by weight of the adhesive layer.The hydrophobic colloidal silica in the adhesive layer retards diffusionof a drug through the adhesive layer by adsorbing the drug. Since theconcentration of drug in the adhesive layer is less than theconcentration of drug in the reservoir layer, a smaller concentration ofhydrophobic colloidal silica is required to adsorb drug in the adhesivelayer than in the reservoir layer. The hydrophobic colloidal silica inthe adhesive layer may be used to adsorb drug present in the adhesivelayer at the time the transdermal system is manufactured, or to adsorbdrug which diffuses into the adhesive layer from the reservoir layerafter the transdermal system is manufactured.

Also, drug crystallization, which is a serious physical appearance issuein transdermal systems, was controlled by using an additional adhesivelayer laminated to the reservoir layer. In addition, this bilayerapproach resulted in improved tack compared to a monolayer approach andsolved the problem of delamination.

Various embodiments disclosed herein relate to a process by which in atransdermal system, a mixture of a polyisobutylene adhesive, anadsorbent capable of adsorbing an active pharmaceutical, and mineral oilact as a drug reservoir for an active pharmaceutical ingredient of lowmelting point. In various embodiments, particularly embodiments in whichthe active pharmaceutical is hydrophobic or is easily hydrolyzed, theadsorbent is a hydrophobic adsorbent, such as hydrophobic colloidalsilica. The active pharmaceutical ingredient of low melting point is adrug having a melting point of between about 20° C. and about 150° C.,or between about 20° C. and about 80° C. In various embodiments, thedrug of low melting point exists in a liquid or oil state at or slightlyabove room temperature, and may melt during storage. In variousembodiments, the drug of low melting point has a melting point aboveroom temperature, but less than temperatures experienced duringprocessing. Accordingly, the drug can change its physical state fromsolid to liquid, and possibly even to gaseous form, depending upon theprocessing conditions or storage conditions. If the drug exists inliquid or oily form during manufacture or storage, the active ingredientmay plasticize the hydrophobic matrix. Since the mineral oil alreadyacts as a plasticizer, the combination of mineral oil and an oily drugcan plasticize the reservoir matrix to the point that dimensionalstability of the matrix is lost. The matrix may undergo cold flow duringstorage, allowing the matrix to expand in length or width to the pointthat the adhesive reservoir expands beyond the boundaries of thedrug-impermeable backing layer.

Additionally, the presence of drug in the liquid form or in an oil formcan allow the drug to diffuse the matrix as a non-solid material, andcause film formation or deposition of the liquid or oil at thereservoir-release liner interface or at the reservoir-backing layerinterface. This can cause solidification and/or crystallization of thedrug at the interface between layers, or formation of a liquid or oildrug layer at the interface between layers. The presence of solid orliquid drug at the interface between layers can reduce the area ofdirect contact between layers, and lead to reduced adhesion at thereservoir-release liner interface or at the reservoir-backing layerinterface. In extreme cases, such reduced adhesion can causedelamination of layers during storage. Accordingly, the presence of drugin an oily or liquid form can lead to poor physical performance of thetransdermal system, including delamination and loss of dimensionalstability.

In various embodiments, the hydrophobic matrix for the reservoir layermay be made by mixing a polymer such as polyisobutylene, mineral oil,hydrophobic colloidal silica, and a drug under high shear conditions. Invarious embodiments, the hydrophobic matrix for the reservoir layer maybe made by mixing polyisobutylene, mineral oil, hydrophobic colloidalsilica, and a drug in a batch process high-shear rotor-stator mixer. Insuch a mixer, the rotor blades turn within a close tolerance stator. Thesmall gap between the blades and the stator, coupled with highrotational speeds, allows for homogenization of polymer blends, e.g.,polyisobutylene/mineral oil blends. The high-shear rotor-stator mixeralso serves to break up silica agglomerates and uniformly disperse thehydrophobic colloidal silica and drug in the hydrophobic polyisobutylenematrix. After preparation of the hydrophobic matrix under high shear,the hydrophobic matrix polymer may be deposited on a drug-impermeablebacking layer, and a release liner is then applied to the exposedsurface of the hydrophobic matrix layer.

In various embodiments, the hydrophobic matrix for the reservoir layermay be made by mixing a polymer such as polyisobutylene, mineral oil,hydrophobic colloidal silica, and a drug in an extruder. In variousembodiments, the hydrophobic matrix for the reservoir layer may be madeby mixing polyisobutylene, mineral oil, hydrophobic colloidal silica,and a drug under elevated temperatures in an extruder, and extruding theresulting mixture to form a reservoir layer. The drug may be added tothe mixture as a solid, which then melts when exposed to elevatedtemperatures in the extruder. Upon cooling, the drug may be dispersed inthe reservoir matrix as an oil or as a liquid.

Uniform distribution of the drug molecules with the hydrophobiccolloidal silica can only be ensured with a well-optimized mixingstrategy. The drug molecules can be uniformly distributed over thehydrophobic colloidal silica particles. In various embodiments,hydrophobic colloidal silica and a hydrophobic drug can be mixed into ahydrophobic polymeric composition in an extruder. Mixing in the extruderhomogeneously disperses the hydrophobic colloidal silica and thehydrophobic drug in the hydrophobic polymeric composition. Homogeneousdispersion of the hydrophobic colloidal silica and the drug in thismanner allows the drug to adsorb to the hydrophobic colloidal silica.The resulting composition may be extruded as a hydrophobic matrix layer.

In various embodiments, the extruded hydrophobic matrix layer isdeposited on a drug-impermeable backing layer, and a release liner isthen applied to the exposed surface of the hydrophobic matrix layer. Insome embodiments, the hydrophobic matrix layer and the hydrophilicbacking layer are coextruded to form a laminate, and a release liner isthen applied to an exposed surface of the hydrophobic matrix layer.

In various embodiments, the reservoir matrix is a combination ofpolyisobutylene and mineral oil. Hydrophobic silica material ishomogeneously dispersed through the reservoir matrix. The hydrophobicsilica material has a strong interaction with the oily or liquidhydrophobic active pharmaceutical ingredient dispersed in the matrix.More specifically, at least a portion of the oily or liquid hydrophobicactive pharmaceutical is adsorbed to the hydrophobic silica material,thereby preventing or reducing diffusion of the active pharmaceuticalthrough the hydrophobic matrix. Additionally, oily or liquid hydrophobicactive pharmaceutical which has been adsorbed to the hydrophobic silicamaterial behaves as a solid material and has a reduced tendency toplasticize the reservoir matrix. Accordingly, adsorption of an oily orliquid drug to hydrophobic colloidal silica, or to a similar adsorbent,reduces delamination and loss of dimensional stability in the resultingtransdermal system.

To manufacture an acceptable transdermal system with an activepharmaceutical ingredient having low melting point, the polyisobutyleneadhesive, hydrophobic colloidal silica and mineral oil combination wasconsidered as a carrier for the dispersed/modified active ingredient inits oil state. The interaction of the polyisobutylene and thehydrophobic colloidal silica with the mineral oil was considered verysignificant in influencing the physical properties of the wholetransdermal system. The silica materials can provide a physicallyacceptable transdermal system for an active ingredient which is in theoil state with the combination of polyisobutylene and mineral oil.Especially, the hydrophobic silica material can provide an acceptabletransdermal system both physically and chemically. This fact isespecially true if the active pharmaceutical ingredient is easily proneto hydrolytic degradation. While many materials are able to adsorbhydrophobic drugs, including colloidal silica, hydrophobic excipientssuch as hydrophobic colloidal silica have the advantage that they do notalso adsorb water. Use of a hydrophilic excipient to adsorb a drug canresult in adsorption of both the drug and water to the excipientsurface, thereby increasing the likelihood of hydrolysis of the drug bythe water. In some cases, the adsorbent actually catalyzes hydrolysis ofthe drug by the water. Since a hydrophobic excipient, such ashydrophobic colloidal silica, does not adsorb water, adsorption of adrug to a hydrophobic excipient does not increase the likelihood ofhydrolysis of the drug.

Additionally, a hydrophilic excipient contains a significant amount ofadsorbed water, while a hydrophobic excipient contains a much smalleramount of adsorbed water. Thus, use of a hydrophilic excipientintroduces more water into the transdermal system than a hydrophobicexcipient. Adding a hydrophilic excipient to a hydrophobic drugreservoir causes addition of water to the reservoir layer, therebyincreasing the extent of drug hydrolysis. Adding a hydrophobic excipientto a hydrophobic drug reservoir does not add significant water to thereservoir layer, and therefore does not increase the extent of drughydrolysis. Thus, the stability of the drug depends upon the adsorbedmoisture on the excipient surface, as well as free moisture present inthe system.

The drug degradation by hydrolysis is mainly determined by the moisturepresent in the pharmacologically active and inactive ingredients or bythe moisture present in the system. The hydrophilic nature of theadhesive and the excipients as well as the amount of moisture present oradsorbed on the silica particles during the processing and storageconditions can directly influence the stability of the adsorbed drug.

Further, a layer of a release-controlling hydrophobic polymeric materialmay be present in between the hydrophobic reservoir matrix and therelease liner. Upon removal of the release liner, therelease-controlling hydrophobic polymeric material layer acts as askin-contacting adhesive layer. In various embodiments, the hydrophobicreservoir matrix and the layer of a release-controlling hydrophobicpolymeric material may be made of substantially the same polymericmaterial, or from different polymeric materials.

In various embodiments, both the hydrophobic reservoir matrix and thelayer of a release-controlling hydrophobic polymeric material contain acombination of polyisobutylene and mineral oil in a weight ratio ofmineral oil to polyisobutylene of between about 0.05:1 and about 1:1,preferably between about 0.25:1 and about 0.60:1, more preferablybetween about 0.30:1 and about 0.50:1. The hydrophobic reservoir matrixadditionally contains a hydrophobic drug and from 8% to 20% by weight ofa hydrophobic excipient capable of adsorbing the drug. The layer of therelease-controlling hydrophobic polymeric material additionally containsfrom 0.5% to 5%, preferably 1% to 3%, by weight of a hydrophobicexcipient capable of adsorbing the drug in the hydrophobic reservoirmatrix. The layer of the release-controlling hydrophobic polymericmaterial may be manufactured without a drug, or including an amount ofdrug which is smaller than the amount of the drug in the hydrophobicreservoir matrix layer in the event that the layer of therelease-controlling hydrophobic polymeric material is manufacturedwithout a drug, the layer of the release-controlling hydrophobicpolymeric material may include a small amount of drug at the time of usedue to diffusion of drug from the reservoir layer during storage.

The layer of the release-controlling hydrophobic polymeric material actsto control release of the drug from the reservoir layer both duringstorage and during use. The release-controlling hydrophobic polymericmaterial provides an additional layer of polymeric material throughwhich the drug must diffuse to reach the release liner during storage,or to reach a skin surface during use of the transdermal system.Additionally, the release-controlling hydrophobic polymeric materialcontains hydrophobic colloidal silica, which acts to adsorb the drug asit diffuses through the release-controlling hydrophobic polymeric layer,thereby slowing diffusion of the drug through the release-controllinghydrophobic polymeric layer.

In various embodiments, the hydrophobic reservoir matrix layer and therelease-controlling hydrophobic polymeric material may be separatelyextruded, and then laminated together. Alternatively, the hydrophobicreservoir matrix layer and the release-controlling hydrophobic polymericmaterial may be co-extruded to produce a laminate. The resultinglaminate is deposited on a drug-impermeable backing layer so that anexposed surface of the reservoir matrix layer contacts the backinglayer, and a release liner may then be applied to an exposed surface ofthe release-controlling hydrophobic polymeric material layer. In someembodiments, the release-controlling hydrophobic polymeric material, thehydrophobic matrix layer and the hydrophilic backing layer arecoextruded to form a laminate with an exposed adhesive surface of therelease-controlling layer. A release liner is then applied to an exposedsurface of the release-controlling layer.

Examples of Transdermal Patches with Hydrophobic Matrix Layers Laminatedto a Release Liner

A series of transdermal patches was prepared, as shown in Table 1. Each,transdermal patch included a hydrophobic matrix layer, adrug-impermeable backing laminated to one surface of the hydrophobicmatrix layer, and a release liner laminated to the other surface of thehydrophobic matrix layer. The hydrophobic matrix layer containedmethylphenidate as a hydrophobic drug in an amount of between 8% byweight and 20% by weight. In various examples, the hydrophobic matrixlayer also contained a combination of mineral oil (MO) andpolyisobutylene (PIB) as a polymeric matrix, in a weight ratio of MO:PIBof between about 0.09:1 and about 1.1:1.

In various comparative examples (identified in Table 1 as “Comp.”), thehydrophobic matrix layer contained hydrophobic colloidal silica in anamount of between 0% by weight and 5% by weight. The comparativeexamples showed poor stability upon storage under accelerated storageconditions. After storage under accelerated storage conditions, thecomparative examples showed evidence of dimensional change duringstorage, due to cold flow of the hydrophobic matrix layer. Additionally,the release layers on the comparative examples were removed afterstorage, and the exposed surfaces of the hydrophobic matrix layers wereexamined. In several cases, evidence of oily or liquid layers at theinterfaces between the release layers and the hydrophobic matrix layerswere observed. Additionally, some comparative examples showedcrystallization of methylphenidate at the surfaces of the hydrophobicmatrix layers. The comparative examples showed frequent evidence ofrelease layer delamination, or premature delamination of the releaselayer. In short, with levels of hydrophobic colloidal silica of 5 wt. %or less, the physical and chemical properties of the transdermal systemwere poor.

In various working examples, the hydrophobic matrix layer containedhydrophobic colloidal silica in an amount of between 8% by weight and30% by weight. The working examples showed good stability upon storageunder accelerated storage conditions. After storage under acceleratedstorage conditions, the working examples showed little or no evidence ofdimensional change during storage under accelerated storage conditions.Additionally, the working examples showed little increase in ease ofrelease layer delamination, or premature delamination of the releaselayer, after storage under accelerated storage conditions. Finally, therelease layers on the working examples were removed, and the exposedsurfaces of the hydrophobic matrix layers were examined. Little or noevidence of oily or liquid layers at the interfaces between the releaselayers and the hydrophobic matrix layers was observed in most cases.Additionally, minimal crystallization of methylphenidate at the surfacesof the hydrophobic matrix layers was observed. Upon increasing thelevels of hydrophobic colloidal silica in the hydrophobic matrix layerto between 8% by weight and 30% by weight, the physical and chemicalproperties of the transdermal system showed significant improvement,when compared to the comparative examples.

TABLE 1 Transdermal Methylphenidate Formulations Example HCS MineralPolybuta- MO:PIB Number Drug (%) (%) Oil (%) diene (%) Results RatioComp. 1 20.00 3.00 20.00 57.00 X 0.35 Comp. 2 20.00 1.00 20.00 59.00 X0.34 Comp. 3 20.00 1.00 40.00 39.00 X 1.03 Comp. 4 20.00 3.00 40.0037.00 X 1.08 Comp. 5 20.00 2.50 20.00 57.50 X 0.35 Comp. 6 16.00 3.0027.00 54.00 X 0.50 Comp. 7 13.00 3.00 28.00 56.00 X 0.50 Comp. 8 16.003.00 20.00 61.00 X 0.33 Comp. 9 10.00 1.00 29.67 59.33 X 0.50 Comp. 1016.00 1.00 27.67 55.33 X 0.50 Comp. 11 16.00 3.00 27.00 54.00 X 0.50 120.00 10.00 20.00 50.00 ◯ 0.40 2 16.00 9.00 25.00 50.00 ◯ 0.50 3 18.0010.00 24.00 48.00 ◯ 0.50 4 14.00 20.00 22.00 44.00 ◯ 0.50 5 18.00 20.0020.67 41.33 ◯ 0.50 6 18.00 20.00 5.00 57.00 ◯ 0.087 7 18.00 20.00 10.0052.00 ◯ 0.19 8 18.00 20.00 17.33 44.67 ◯ 0.39 Comp. 12 20.00 0.00 20.0060.00 X 0.33 Comp. 13 20.00 0.00 40.00 40.00 X 1.00 Comp. 14 20.00 5.0040.00 35.00 X 1.14 Comp. 15 8.00 0.00 30.65 61.35 X 0.50 Comp. 16 16.000.00 28.00 56.00 X 0.50 Comp. 17 16.00 5.00 26.33 52.67 X 0.50 Comp. 1810.00 5.00 28.33 56.67 X 0.50 9 20.00 20.00 16.00 44.00 ◯ 0.36 10  20.0010.00 18.67 51.33 ◯ 0.36 11  18.00 30.00 17.33 34.67 ◯ 0.50 HCS:Hydrophobic colloidal silica X: Adhesive matrix showed poor stability.Transdermal patches showed release layer delamination or dimensionalchange in the reservoir matrix under accelerated stability storageconditions. ◯: Adhesive matrix showed good stability. Transdermalpatches showed little or no release layer delamination or dimensionalchange in the reservoir matrix under accelerated stability storageconditions.Examples of Transdermal Patches with Hydrophobic Matrix Layers Laminatedto a Drug-Free Adhesive Skin Contact Layer

Transdermal patches were prepared including a hydrophobic matrix layer,also referred to as a drug reservoir layer; a drug-impermeable backinglaminated to one surface of the hydrophobic matrix layer; and a releaseliner. In between the hydrophobic matrix layer and the release liner,there was a drug-free adhesive skin contact layer. The adhesive skincontact layer helps to control the rate of diffusion of methylphenidatefrom the transdermal patch, and is therefore also referred to as arate-limiting layer.

The hydrophobic matrix layer contained methylphenidate as a hydrophobicdrug in an amount of 18% by weight. The hydrophobic matrix layer alsocontained a combination of mineral oil (MO) and polyisobutylene (PIIS)as a polymeric matrix. Specifically, the transdermal patch contained18.00% methylphenidate and 20.00% hydrophobic colloidal silica in thedrug reservoir layer and 2.00% hydrophobic colloidal silica and 0%methylphenidate in the adhesive skin contact layer, as seen in Table 2.

Table 2 presents two transdermal patch formulations. Each formulation isa bilayer composition, including a hydrophobic matrix layer, or drugreservoir layer, and an adhesive skin contact layer. The hydrophobicmatrix layer is identical in each formulation. The rate limiting layersin the two formulations are identical in composition, but are coated todifferent thicknesses. In the formulations of Table 2, methylphenidateis present in the drug reservoir layer as a dispersed solid that isabsorbed onto the surface of hydrophobic colloidal silica. In theformulations of Table 2, methylphenidate is not fully dissolved in thepolymer matrix, and there are no visible drug crystals in thetransdermal patch formulation.

TABLE 2 Transdermal Methylphenidate Formulations Containing an AdhesiveSkin Contact Layer Prototype 1 Prototype 2 % w/w gsm % w/w gsm RateLimiting Layer 33.33% 30 53.85% 70 Methylphenidate  0.00% 0.00  0.00%0.00 Hydrophobic Colloidal Silica NF  2.00% 0.60  2.00% 1.40 (AerosilR972 Pharma) Light Mineral Oil NF 32.67% 9.80 32.67% 22.87 (Drakeol 7)Polyisobutylene Adhesive 65.33% 19.60 65.33% 45.73 (Duro-Tak ™ 87-613A)Drug Reservoir Layer 66.67% 60 46.15% 60 Methylphenidate 18.00% 10.8018.00% 10.80 Hydrophobic Colloidal Silica NF 20.00% 12.00 20.00% 12.00(Aerosil R972 Pharma) Light Mineral Oil NF 20.67% 12.40 20.67% 12.40(Drakeol 7) Polyisobutylene Adhesive 41.33% 24.80 41.33% 24.80(Duro-Tak ™ 87-613A) Combined Laminate  100% 90  100% 130Methylphenidate 12.00% 10.80  8.31% 10.80 Hydrophobic Colloidal SilicaNF 14.00% 12.60 10.31% 13.40 (Aerosil R972 Pharma) Light Mineral Oil NF24.67% 22.20 27.13% 35.27 (Drakeol 7) Polyisobutylene Adhesive 49.33%44.40 54.25% 70.53 (Duro-Tak ™ 87-613A)

By adding another adhesive layer, which is the skin contact layer, tothe hydrophobic matrix layer, the laminated hydrophobic matrix layer andadhesive skin contact layer in the finished dosage form showed goodstability and showed little or no tendency to form oily layers orcrystals at the interface between the skin contact layer and the releaseliner. Specifically, no crystals were observed at the interface betweenthe skin contact layer and the release liner under room temperature andrefrigerator storage conditions. However, at extreme storage conditions,such as storage in a freezer, e.g., at temperatures of −20° C.,formation of crystals was sometimes observed.

In general, both the working examples of Table 1 and the examples ofTable 2 were superior to the comparative examples of Table 1. Thecomparative examples of Table 1 had a greater tendency to form oilylayers or crystals at the interface between the hydrophobic matrixlayer, or drug reservoir layer, and the release liner than either theworking examples of Table 1 or the examples of Table 2. Accordingly,inclusion of high levels of hydrophobic excipients, includinghydrophobic colloidal silica, in the drug reservoir layer stabilizes thetransdermal dosage form by reducing or preventing free diffusion ofhydrophobic drugs through the hydrophobic matrix. Also, the examples ofTable 2 were superior to both the comparative examples and workingexamples of Table 1. Accordingly, a drug-free skin contacting adhesivelayer containing a low level of hydrophobic excipients, includinghydrophobic colloidal silica, further stabilizes the transdermal dosageform by reducing or preventing diffusion of hydrophobic drugs from thehydrophobic matrix to the interface with the release liner.

Although the various exemplary embodiments have been described in detailwith particular reference to certain exemplary aspects thereof, itshould be understood that the invention is capable of other embodimentsand its details are capable of modifications in various obviousrespects. As is readily apparent to those skilled in the art, variationsand modifications can be affected while remaining within the spirit andscope of the invention. Accordingly, the foregoing disclosure anddescription are for illustrative purposes only and do not in any waylimit the invention, which is defined only by the claims.

What is claimed is:
 1. A hydrophobic patch for transdermaladministration of a hydrophobic drug, comprising: a hydrophobicreservoir having a first surface and a second surface; a backing layeroverlying said first surface, said backing being impermeable to saiddrug; and optionally a release sheet overlying said second surface; saidhydrophobic reservoir comprising a hydrophobic matrix and saidhydrophobic drug, said drug being homogeneously dispersed through saidhydrophobic matrix, said hydrophobic matrix comprising: from about 9% toabout 30% by weight of said reservoir of hydrophobic colloidal silicadispersed through said hydrophobic matrix; and a mixture of mineral oiland polyisobutylene; wherein said hydrophobic colloidal silica adsorbsat least a portion of said drug; and wherein a weight ratio of saidmineral oil to said polyisobutylene is between about 0.087:1 and about0.50:1.
 2. The hydrophobic patch of claim 1, wherein said weight ratioof said mineral oil to said polyisobutylene is between about 0.30:1 andabout 0.50:1.
 3. The hydrophobic patch of claim 1, further comprising arelease-controlling adhesive layer in contact with said second surface,with the proviso that if said release sheet is present, saidrelease-controlling adhesive layer is between said hydrophobic reservoirand said release sheet.
 4. The hydrophobic patch of claim 3, whereinsaid release-controlling adhesive layer comprises: from about 0.5% toabout 5% by weight of said release-controlling adhesive layer ofhydrophobic colloidal silica; and a mixture of mineral oil andpolyisobutylene in a weight ratio of said mineral oil to saidpolyisobutylene of between about 0.05:1 and about 0.50:1.
 5. Thehydrophobic patch of claim 4, wherein said hydrophobic matrix in saidhydrophobic reservoir comprises from about 9% to about 20% by weight ofhydrophobic colloidal silica; and said release-controlling adhesivelayer comprises from about 0.5% to about 4% by weight of hydrophobiccolloidal silica.
 6. The hydrophobic patch of claim 1, wherein saidhydrophobic drug is a hydrophobic drug which is able to diffuse throughsaid hydrophobic matrix.
 7. The hydrophobic patch of claim 1, whereinsaid hydrophobic drug has a melting point of between 20° C. and 150° C.8. The hydrophobic patch of claim 7, wherein said hydrophobic drug ismethylphenidate, ibuprofen, clonidine, or scopalamine.
 9. Thehydrophobic patch of claim 7, wherein said hydrophobic drug ismethylphenidate.
 10. The hydrophobic patch of claim 1, wherein saidhydrophobic colloidal silica has a mean particle size of between about30 nm and about 150 nm.
 11. The hydrophobic patch of claim 1, whereinsaid hydrophobic colloidal silica is colloidal silica which has beentreated with a silane of formula I:R_((4-n))SiX_(n)  I where R is a C1 to C20 alkyl or aromatic group, X isa hydrolysable group, and n is 1, 2, or
 3. 12. The hydrophobic patch ofclaim 11, wherein X is —OH, —O₂CR¹, —Cl, —Br, —I, —OR¹, —COR¹, —NHR¹, or—NR¹ ₂ , where R¹ is a C1 to C20 alkyl group.
 13. The hydrophobic patchof claim 1, wherein the hydrophobic reservoir is a skin-contactingadhesive layer.
 14. A hydrophobic patch for transdermal administrationof a hydrophobic drug, wherein said hydrophobic drug is an oil or a drughaving a melting point between about 20° C. and about 150° C.,comprising: a hydrophobic reservoir comprising said hydrophobic drug,said reservoir having a first surface and a second surface; a backinglayer overlying said first surface, said backing being impermeable tosaid hydrophobic drug; and optionally a release sheet overlying saidsecond surface; said hydrophobic reservoir comprising said hydrophobicdrug and a hydrophobic matrix, said hydrophobic matrix comprising: amixture of mineral oil and polyisobutylene in a weight ratio of saidmineral oil to said polyisobutylene of between about 0.087:1 and about0.50:1; and an excipient or filler in an amount which is effective toadsorb said hydrophobic drug, thereby preventing said drug from forminga liquid or oily layer at the interface between said hydrophobicreservoir and said release sheet or said backing; said excipient orfiller being hydrophobic colloidal silica in an amount of about 9% toabout 30%.
 15. The hydrophobic patch of claim 14, wherein saidhydrophobic drug and said excipient or filler are present in a weightratio of between about 2:1 and about 0.9:1.
 16. The hydrophobic patch ofclaim 14, wherein said excipient or filler further comprises at leastone material selected from the group consisting of: neusilin (magnesiumaluminometasilicate) in an amount of about 2% to about 5%; a combinationof neusilin (magnesium aluminometasilicate) in an amount of about 2% toabout 5% and at least one of magnesium stearate in an amount of about 2%to about 5% and polyethoxylated castor oil in an amount of about 2% toabout 5%; colloidal silica or dried colloidal silica in an amount ofabout 1% to about 10%; a combination of colloidal silica in an amount ofabout 1% to about 3% and at least one of neusilin in an amount of about2%, magnesium stearate in an amount of about 1% to about 3%, disodiumhydrogen phosphate in an amount of about 2% to about 5%, andpolyethoxylated castor oil in an amount of about 2% to about 5%;disodium hydrogen phosphate in an amount of about 2% to about 5%;anhydrous calcium phosphate dibasic in an amount of from 5% to about10%; a combination of anhydrous calcium phosphate dibasic in an amountof from 5% to about 10% and polyethoxylated castor oil in an amount ofabout 2% to about 5%; polyethoxylated castor oil in an amount of about2% to about 5%; magnesium stearate in an amount of about 2% to about 5%;clays in an amount of about 5% by weight; up to 1% by weight ofalpha-tocopherol; and from about 5% to about 20% of a cationic copolymercomprising dimethylaminoethyl methacrylate, butyl methacrylate, andmethyl methacrylate; wherein all percentages are based on the weight ofthe hydrophobic reservoir.